Medial part thickness of wearable device affecting running motion

Abstract

This paper reports negative effects on runner’s motions which are supported by an exoskeleton attached to his/her lower limbs. A wearable assistive device has generally been developed to support motions of a wearer, while the device may disturb wearer’s motions due to physical features, including expanded his/her body outline and device’s weight. The expanded outline can exert adverse influence that limits range of motion of a wearer. In this paper, we focus on lower limb motions of a runner who puts an exoskeleton on his/her lower limbs to receive physical assistance. We simulated influence of medial parts of the exoskeleton on running through experiments with seven runners wearing one of three couples of rectangular-shaped light blocks (10 mm, 20 mm or 30 mm in thickness) on the medial sides of both thighs. These blocks increased step width but the 30 mm-thick blocks only increased net running heat rates by 6.05 bpm compared with that of running without blocks. This result shows that a wearable device which is equipped with components less than 20 mm-thick on each medial part of a runner’s thigh has little detrimental effects on running motions.

Introduction

Researchers have developed devices augmenting and supporting healthy human motions including lifting up, hopping and walking [1]. A target motion to be augmented has shifted from static motions to dynamic motions. Grabowski and Herr [2] developed an exoskeleton for supporting human hopping. This exoskeleton attached parallel springs to wearer’s legs and supported leg motions. It reduced net metabolic power by 24% compared with that during hopping without the exoskeleton. For walking assistance, Kitatani et al. [3] developed a powered device which supported hip joint extension and flexion. They measured oxygen consumption during walking at comfortable speed with or without the device. This assistive device was reported to reduce net oxygen consumption by 7.06% during walking at comfortable speed compared with that without the device. Collins et al. [4] developed an unpowered exoskeleton assisting walking. This exoskeleton supported plantar flexion of the ankle joints with springs, and reduced net metabolic power during walking by \(7.2\pm 2.6\)% compared with that without it. Luke et al. [5, 6] developed a powered walking assistance device supporting plantar flexion of the ankle joints. They reported that their device reduced net metabolic cost during walking by \(11\pm 4\)% compared with that without it. Kim et al. [7, 8] have developed a running assistance device supporting hip joint extension. This device powered to drive actuators reduced net metabolic power during running by 3.9% and 8.2% compared with that without the device and that with the unpowered device, respectively. They reported negative effects of this device, increasing metabolic power with un-actuated device from that without the device.

The purpose of these assistive devices is to reduce human effort for motions. Eventual effects of the devices are summation of positive effects and negative effects of the devices. To increase the eventual effects, increase in positive effects and decrease in negative effects are required. This paper focuses on reducing the negative effects on running to increase the eventual effects. Mass and its distribution of the device are important for in the negative effects’ reduction. Bourdin et al. [9] measured the effects on running at 5 m/s by weight jackets, called vertical loading. They reported that the jacket which was 10% weight of body weight increased net energy cost by 4.6% compared with that without the jacket. Martin [10] evaluated the effects by additional weights on thighs, shanks and feet. This research reported that 1.0 kg weights attached to each foot and thigh increased oxygen consumption of runners by 7.2% and 3.5% compared with that without any weights, respectively. The oxygen consumption with load was reported to linearly increase according to mass between 0.0 and 1.0 kg on feet and thighs. This research showed relationship between metabolic demand and two properties of objects attached to the legs: weights and positions.

Since effects of additional weight on a runner have been reported, designers of assistive devices can estimate negative effects of device’s weight. On the other hand, effects of volume of the device on a runner have not reported. Range of motion of a person who wears an exoskeleton on his/her body may be limited because his/her expanded body tends to collide with each other. This limitation becomes severer at a close area between body parts, such as knee and ankle. For example, medial parts of a wearable device attached to the legs are expected to increase step width, distance on the mediolateral axis between right and left foot landing points, during running due to reduced margin between the legs. The medial parts are essential for structure design of attachments and medial joints of the devices around knee and ankle joints. Walking and running with wider step width than normal one need higher metabolic power [11, 12]. In this paper, we measure motions and heart rates during running experiments with blocks attached to medial sides of the thighs. We propose design requirements about the shape of wearable devices supporting running motions to reduce negative effects of the devices. These devices are supported to be used by healthy adult people who are commuting and delivering mails for lower running energy cost.

Experimental setup

Subjects

Seven healthy male runners served as subjects for this study. Table 1 shows the subject measurements, and Fig. 1 shows definition of the variables. The leg length (LL) is distance between a maker on the most lateral prominences of the grater trochanter (GT) and the ground in an upright position. The thigh length is distance between the GT and a marker on the lateral epicondyle of the femur. Block position is distance between the GT and the center of the blocks on the proximodistal axis of the legs. Knee width is distance between the most lateral prominence of the lateral femoral epicondyle and the medial prominence of the medial femoral epicondyle. All the subjects were right-legged runners. Informed consent was obtained from all subjects prior to their participation in the study. The experiments of this study were approved by the ethics committee of Nagoya University.

Definition of variables of subject measurements and additional block position. These green circles represent makers for a motion capture system. The picture represents a subject standing upright. These additional blocks are on medial surface of the thighs

Test procedures

Four conditions were employed to examine effects by medial parts attached to the legs. A subject ran wearing one of following objects on each thigh: (1) no block, (2) 10 mm-thick blocks, (3) 20 mm-thick blocks and (4) 30 mm-thick blocks. Figure 2a shows the blocks. The subjects putted the blocks on medial sides of the thighs using tapes, and these tapes were slack enough for muscle contraction (Figs. 1, 2b). The location of the blocks was a little proximal knee joints position in order not to disturb knee flexion. The weights of the 10 mm-thick block, 20 mm-thick one and 30 mm-thick one are 17 g, 23 g and 29 g, respectively. The weight of these blocks has little effects on running motions. The height and width of all blocks are 60 mm and 40 mm, respectively. Block height and width were designed for avoiding its rotation on the thigh and attaching easily. The block edges are tapered to slide each other when they collide.

Fig. 2

Additional blocks attached to the thighs. a Additional blocks with three thickness. The thicknesses of blocks were 10 mm, 20 mm and 30 mm from left, respectively. The blocks were rounded not to harm wearers. The unit of the ruler was millimeters. b A block attached to the right thigh with tapes. The tape passed around the thigh

Each subject performed a trial in a day consisted of four bouts of 7-min running on a treadmill. Each bout was separated by at least 10-min resting interval, and each trial was separated by at least 1-day interval. Subjects performed four trials under each condition. The order of the conditions for a subject was randomly selected. Running speed in all bouts was 2.5 m/s (9 km/h). The subject ran without additional volume in the first bout (normal running). After this bout, the subject performed the other three bouts under selected condition out of four. The first bout was a control bout to obtain heart rates during normal running. The subjects were instructed to keep running speed constant and to run as usually as possible.

Measurement systems

Figure 3 shows axes and planes in the experiments. Running direction and the vertical axis were defined as x-axis and y-axis, respectively.

Planes and axes around a runner and a running environment. In this paper, x-axis is a running direction of a treadmill and x–z plane is upper face of the treadmill belt. An origin of the coordinate system is a left rear corner of the treadmill

A motion capture system (Motive, NaturalPoint, USA) was used to record the running motions. All cameras of the system (Flex 13, NaturalPoint, USA) captured 120 frames every second. A marker arrangement for the subjects was Rizzoli Lower Body Protocol [13,14,15], which is used in biomechanical study.

Motions of the subjects were calculated using inverse kinematics (IK) function of an open-sourced software for biomechanical analysis (OpenSim, The National Center for Simulation in Rehabilitation Research, USA). The IK function used a three-dimensional skeleton model with 23 degree of freedom (Gait2354Model). This skeleton model is standard for studies of gait and designed based on biomechanical studies [16,17,18]. The skeleton model was scaled to fit the subject bodies using marker positions of a static pose of the subjects and this static pose was T-pose. The IK function calculated the posture of the subjects, including joint angles, body parts’ positions and positions of the center of mass (CoM), based on marker trajectories during running. The solved CoM positions on at x-axis and z-axis were band-pass filtered (1.0–6.0 Hz) to remove noise and motions which periods were longer than stride time.

The subject wore a three-axes acceleration sensor on their right shoe to detect heel strikes. This sensor recoded acceleration at 142.86 Hz sampling frequency and its sensing range was ±156.96 m/s2 (± 16 gravity acceleration). The acceleration signals were high-pass filtered (60 Hz) to remove signals during leg swinging. In the experiment, heel strikes detected as peaks of acceleration norm. Gait cycle ratio (GCR) represents phases of running motions. GCR of 0% means a heel strike of the right leg and GCR of 100% means next one.

To obtain averaged signals during a single running cycle, signals were divided into one hundred parts according to GCR and averaged in each part. When we evaluated maximum and minimum values during a single running cycle, we calculated these from the divided values. To evaluate motions during a steady state, the values during 4–7 min were calculated.

A heart rates sensor using signals in an electrocardiogram (Polar H10, Polar Electro, Finland) was used to record metabolic demand of the subjects during the experiments. This sensor outputted data every 1 s. The heart rates of the subject gradually increased from a beginning of running to approximately 3 min after the beginning and then became saturated. To evaluate the metabolic demand for steady running, the mean of measured heart rates during 4–7 min was used for evaluation. To evaluate metabolic demand for running, we used net running heart rates which is calculated as heart rates minus the rates during the normal running on the same experimental day [19].

Statistical analysis

To evaluate difference in data among each condition, variables were statistically analyzed with the repeated measures analysis of variance (RM-ANOVA). In this paper, significance level, 0.05, was used for all statistical tests to determine significant difference. When RM-AROVA showed significant difference in groups, paired t-test evaluated difference in couples of groups.

Difference in each condition was sparsely analyzed at GCR of 0, 25, 50 and 75%. The instants at 0, 25, 50 and 75% GCR represent characteristic events during running including, heel strike of right, the maximum knee flexion of right during the stance phase, the heel strike of left and the maximum knee flexion of left during the stance phase, respectively.

Results

As shown in Table 2 and Fig. 4, the mean of the net running heart rates in the condition of 30 mm-thick blocks was 6.05 bpm higher than that in the condition of no block (\(P = 0.023\)). The means of these in the conditions of 20 mm-thick blocks and 10 mm-thick blocks increased 2.28 and 0.24 bpm, respectively, which had no significant difference. 30 mm-thick blocks increased physical load of running, but 20 mm-thick blocks and 10 mm-thick ones did slightly.

Figure 5 shows hip joint motions in the coronal plane during running. Positive and negative hip adduction angles represent leg adduction and abduction, respectively. The mean of the left hip adduction angle in the condition of 30 mm-thick blocks was 3.50° smaller than that with no block (\(P = 0.009\)). The mean of the angle in the condition of 20 mm-thick blocks and 10 mm-thick blocks increased by − 3.80 and 0.03° compared with the condition of no block, respectively, which had no significant difference. On the other hand, the mean of the right hip adduction angle had no statistically significance between all couples of the conditions. Hip adduction of the subjects was an asymmetric motion. An angle between the thighs in the coronal plane (\(\phi _t\)) is defined as

$$\begin{aligned} \phi _t&= \phi _{r} + \phi _{l}, \end{aligned}$$

(1)

where \(\phi _{r}\) and \(\phi _{l}\) are the right hip adduction angle and left one, respectively. The 30 mm-thick blocks reduced the mean of the thighs angle (\(\phi _t\)) by 4.09° compared with these without the blocks (\(P=0.026\)). The means in the condition of 20 mm-thick blocks and 10 mm-thick blocks decreased by 3.83° and 0.03° compared with the condition of no block, respectively, which had no significant difference. The subjects spread their legs during running with the 30 mm-thick blocks.

The leg motions in the sagittal plane under each condition had little changes (Fig. 6). RM-ANOVA showed no statistically significant differences in the joint angles on the sagittal plane. The blocks in each thickness did not change leg motions in the sagittal plane.

Figure 7 shows relative positions of the knees to the pelvis during running. The 20 mm-thick blocks and the 30 mm-thick ones moved both knee trajectories in lateral direction. At 25% GCR, the 30 mm-thick blocks decreased the mean of the left relative knee z-position by 1.94 %LL (\(P= 0.007\)) compared with the condition of no block. At 75% GCR, the 20 mm-thick blocks and the 30 mm-thick ones increased the means of the right knee relative z-position by 1.75 and 2.36 %LL (\(P= 0.008\) and 0.011) compared with the condition of no block, respectively. The other differences of the right or left relative knee z-position between the condition of no block and the other conditions at the particular GCRs were not significant.

Fig. 7

Horizontal knee relative positions to pelvis during running. These positions described as percentage of leg length (%LL). The red circles and the red squares represent right and left heel strikes, respectively. The arrows represent the direction of motions. This figure demonstrates that runner with 20 mm thick and 30 mm thick blocks makes knees shift in lateral direction for avoiding blocks’ collision

Figure 8 shows relationship between minimum distance between left and right knee positions (d) and block thickness. The means of the minimum knee distance (d) in the condition of 20 mm-thick blocks and the 30 mm ones were 2.02 %LL and 3.11 %LL (\(P= 0.041\) and 0.021) larger than the mean in the condition of no block, respectively. The mean in the condition of 10 mm-thick blocks was 0.70 %LL higher than that in the condition of no block, and this difference was not significant.

where w and t are knee width and block thickness, respectively. The minimum knee clearance (c) represents a clearance between the additional blocks, however, actual block clearance is slightly larger than the minimum knee clearance because the block position is a little closer to the hip joints than knee position. Figure 9 shows relationship between the block thickness and the minimum knee clearance. When the additional blocks thickness increased, the minimum knee clearance decreased. The 10 mm, 20 mm and 30 mm-thick blocks reduced the minimum knee clearance by 1.65, 2.68 and 3.94 %LL (\(P=0.003\), 0.013 and 0.006) compared with that without the blocks, respectively. When the block thickness increased, a margin between the blocks for avoiding these collisions decreased.

Figure 10 shows relative positions of the feet to the pelvis during running. Each origin of foot position is at a center of metacarpophalangeal joint of each index finger. The 20 mm-thick blocks and the 30 mm-thick ones moved right foot trajectory in lateral direction. Only 30 mm-thick block also moved left foot trajectory in lateral direction. At 25% GCR, the 20 mm-thick blocks and the 30 mm-thick ones increased the means of right relative foot z-position by 1.47 and 2.92 %LL (\(P = 0.006\) and 0.002) compared with the condition of no block, respectively. At 75% GCR, 30 mm-thick blocks decrease the position of left by 2.53 %LL (\(P = 0.041\)) compared with the condition of no block. The other differences of the right or left relative foot z-position between the condition of no block and the other conditions at the particular GCRs were not significant.

Fig. 10

Horizontal relative foot positions to pelvis during running. These positions were relative ones to the pelvis position. The red circles and the red square represent right and left heel strike, respectively. The arrows represent the direction of foot motions. This figure demonstrates that runner with 20 mm thick and 30 mm thick blocks moved foot in lateral direction

Figure 12 shows positions of the CoM during running. The CoM positions on x-axis and y-axis in each condition had little difference. The 30 mm-thick blocks increased maximum z-positions of the CoM and decreased minimum ones. Figure 13 shows relationship between the block thickness and z-amplitude of the CoM during running. The 30 mm-thick blocks increased the mean of the amplitude by 0.27 %LL (\(P=0.045\)) compared with that without the blocks. The CoM during running with the 30 mm-thick blocks was strongly accelerated on the mediolateral axis.

Fig. 12

The CoM position during running. The CoM position on x-axis and z-axis were band-pass filtered (1.0–6.0 Hz). The zero position on x-axis and z-axis does not represent the center of body, but means of position during running

Discussion

The joint trajectories and the CoM motion during normal running were reported [20, 21]. The results of the trajectories of normal running in our experiments and these conventional research results were consistent in joint angles and CoM motions.

The blocks on medial side of the thighs can reduce margin between the thighs. To keep running speed constant, runners spread their legs to compensate the margin and to avoid collision of the blocks. There were few collisions between the blocks happened during the experiments, since the subjects had known the size of the attached blocks before running. They unconsciously changed their running motions for the collision avoidance in advance. The thighs angle (\(\phi _t\)) in the conditions of 20 mm-thick blocks and 30 mm-thick ones decreased by 77% and 82% compared with that without blocks, respectively (Fig. 5). This reduction supports the hypothesis that a runner spreads their legs to avoid collision of the blocks.

When the thighs angle decreased, the relative knee joint positions shifted in lateral direction, and minimum knee distance increased to obtain an enough clearance between the blocks for avoiding these collisions. As shown in Fig. 7, the relative knee joint positions during running with the 20 mm and 30 mm-thick blocks moved in lateral direction. When the pelvis rotates, the relative knee joint position moves even if right hip adduction is constant. The means of the pelvis rotation in the condition of 30 mm blocks and 20 mm blocks decreased by 2.71° and 3.04° compared with the condition of no block, respectively. As a result, the right knee relative position moved in the lateral direction.

Trajectories of the knee positions kept these profiles constant in each case. Runners with the blocks do not decrease hip adduction angle in a limited time around the instance when the knees passed each other, because changing the profiles can increase metabolic demand for running. The minimum knee clearance (c) decreased when the thickness of blocks attached to the knees increased. We assume that runners keep the minimum clearance constant by increasing hip abduction angles. However, subjects in these experiments did not actually increase their hip abduction angles. Changing knee joint trajectories from these of normal running increases required human effort. Runners wearing the blocks need both to keep the minimum knee clearance positive and to suppress changing the trajectories. When the block thickness increased in the experiments, the latter’s priority increased.

The hip abduction shifts foot positions in lateral direction and increases the step width. 20 mm-thick blocks moved right foot position in lateral direction, and 30 mm-thick blocks moved both foot positions in lateral direction (Fig. 10). The runners keep horizontal profiles of the foot position constant as well as that of knee.

Amplitude of the CoM position on the mediolateral axis with 30 mm-thick blocks was larger than that without blocks. The amplitude with the 10 mm and 20 mm-thick blocks had no significant difference from that without blocks. Small increase in step width does not increase the amplitude because the runners can keep their pelvis position coincided with that of normal running.

Right knee and foot positions were closer to pelvis positions than left ones. This result shows that right leg was more vertical to the ground in the coronal plane than left ones, and that the CoM position was biased to right. The all subjects’ handed-legs was right, and they mainly used their handed-leg for acceleration of the CoM.

All the net running heart rates in this experiment were higher than 0. Heart rates during running under experimental conditions were higher than that during the first bout. Fatigue of a runner during the first bout increased those. 30 mm blocks increased net running heart rates by 6.05 bpm compared with that without blocks, but the other blocks did not significantly.

Arellano et al. [12] reported U-shaped relationship between net metabolic power and step width. The metabolic power during running assumes to be minimum when a runner takes preferable step width. With increased and decreased step width from preferred one, the metabolic power increases. Change rates of metabolic power increase with increase of step width from preferred one. In our experiment, the additional blocks increased step width of runners. Small increased step widths brought by the 10 mm-thick blocks and the 20 mm-thick ones had less effects on the net running heart rates, because the step widths were close to preferred ones. On the other hand, the 30 mm-thick blocks increased the heart rates, because these step width was far from preferred ones. We assume that the heart rates and the block thickness have also an U-shaped relationship with step width that the heart rates increase sharply between the thickness of 20 mm and 30 mm. Arellano et al. explained that un-preferred step width increases ground reaction force (GRF) in the mediolateral direction and the CoM moment around the anteroposterior axis. GRF in the mediolateral direction increases the CoM amplitude in the mediolateral direction and disturbs effective progress of a runner. When the moment around the anteroposterior axis increases with increase of step width, runners need counter moment to keep their torso orientation upright. Runners with un-preferred step width need high effort for moving forward and keeping the torso orientation. The 30 mm-thick blocks attached to medial sides of the thighs increase CoM amplitude in the mediolateral direction and increased the heart rates.

Conclusion

In summary, our data reveals that 30 mm-thick blocks attached to medial sides of the thighs increased net running heart rates by 6.05 bpm, and amplitude of the CoM on the mediolateral axis [%LL] by 52% compared to these in normal running. On the other hand, the 10 mm-thick blocks and the 20 mm-thick ones did not increase neither net running heart rates and the CoM amplitude. This result shows that running can be disturbed by medial parts of a running assistive device which thickness is more than 30 mm around medial side of the knee joint. To avoid adverse effects on running, thickness of medial parts of the device should be less than 30 mm.

Authors

Search for Naoki Kubota in:

Search for Yasuhisa Hasegawa in:

Contributions

NK designed the experiment, carried out all experiments, analyzed data and wrote the paper. YH initiated this project and gave advises on the design of the experiment, analysis of data and paper writing. Both authors read and approved the final manuscript.

Corresponding author

Ethics declarations

Competing interests

Additional information

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Rights and permissions

Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.